JP2018510380A5 - - Google Patents

Description

Method of determining the optical function of a spectacle lens adapted to a wearer

  The invention relates to a computer implemented method for determining the optical function of a spectacle lens adapted to a wearer. The invention further relates to the use of a spectacle lens comprising an area adapted to at least an intermediate distance field of view, in order to allow the wearer of the spectacle lens to better understand the voice message.

  Usually, people with hearing problems are referred to a physician and the physician performs a hearing test to provide a hearing aid.

  Typically, hearing aids, or hearing aids, are electroacoustic devices, which amplify the sound for the wearer, usually for the purpose of making the speech easier to understand, and the hearing measured in the hearing test Designed to correct the disorder.

Such a hearing aid is efficient, but as a matter of fact causing discomfort to the wearer, it requires the supply of power from a power source and may interfere with other electronic devices such as telephones, radios, etc. there are a number of drawbacks.

Thus, there is a need for a compatible device that can replace existing hearing aids or increase hearing aids for the wearer.

  One object of the present invention is to provide such a compatible device.

To this end, the invention proposes a method, for example implemented by computer means, for determining the optical function of the spectacle lens adapted to the wearer, which method comprises
- a wearer data providing step of wearer data including an indication of ophthalmic formulations indicative of auditory sensitivity of at least the wearer the wearer is provided,
- an optical function determination step of conforming an optical function to the wearer based on at least the wearer data is determined,
including.

The method according to the invention, to determine the hearing sensitivity of the wearer, it proposes to choose the adapted optical design in accordance with this sensitivity.

Advantageously, the method according to the present invention allows a particular wearer with hearing discomfort, for these wearer, to provide a design for the needs of the audiovisual.
The method of the invention may also be used to make the conversation more understandable to a wearer without auditory discomfort.

The solution of the invention is to improve the auditory comfort of the wearer through a single device, discomfort integral hearing aid and glasses have the advantage of avoiding (weight, fit, appearance, etc.).

We, by fitting based on the optical function of the spectacle lens to be provided to the wearer an indication of hearing sensitivity of the wearer, a voice message, emitted otherwise people who are facing the wearer conversation It has been found that the degree of understanding is greatly enhanced.

According to another embodiment, which can be considered alone or in combination:
- the wearer data further includes an indication of the effect of visual indicators give the understanding of the voice message by the wearer, and / or - the optical function determination step, the optical function of the facial expression of the wearer runs to include a fit region so as to facilitate the reading test (labo-facial reading), and / or - the hearing sensitivity of the wearer, wherein provided in the wearer data providing step, at least one It is determined by objective tests, and / or - the objective test is the perception test audio frequency range, and / or - the hearing sensitivity of the wearer provided in the wearer data providing step , it is determined by at least one subjective test, and / or - following the subjective test,
-Evaluation of speech comprehension in noisy environments-Life questionnaire concerning hearing in daily listening situations-Examination of reading test of facial expressions ,
And / or-said optical function determination step comprises the step of selecting an optical function from a predetermined optical function group based on said wearer data, and / or- Or-said optical function determination step comprises the step of determining a transmission function based on said wearer data,
-Said optical function determination step comprises the step of determining a refractive function based on said wearer data.

  According to another aspect, the invention is adapted to at least an intermediate distance field of view so that the wearer of the spectacle lens can better understand the voice message, eg the voice message uttered by the person facing the wearer. The use of a spectacle lens including the

  According to another aspect, the invention is adapted to at least an intermediate distance field of view so that the wearer of the spectacle lens can better understand the voice message, eg the voice message uttered by the person facing the wearer. The present invention relates to an eyeglass lens including a shaded area.

The invention further relates to a spectacle lens adapted to the wearer, comprising at least a median distance vision area adapted to a median distance vision, wherein the transmission function of the spectacle lens makes for example the person's lips visible better through the median distance vision area In order to do so, it is arranged to improve the reading inspection of the facial expressions of the wearer.

  According to an embodiment, the spectacle lens may be colored to enhance the contrast of the lips of the person viewed through the spectacle lens.

The invention further comprises a pair of spectacle lenses adapted to the wearer, at least one of said spectacle lenses having an optical function determined by the method according to the invention.

The present invention further processor comprises one or more conserved instruction sequence is accessible, when executed by the processor, a computer program product for executing the steps of the method according to the invention to said processor.

The present invention also relates to a storage media reading computer program recorded thereon, said program executing the method of the present invention to the computer.

  The invention further relates to an apparatus comprising a processor adapted to store one or more sequences of instructions and to carry out at least one of the steps of the method according to the invention.

  As will be apparent from the following description, unless otherwise clearly stated otherwise, a descriptive statement using "operations", "calculations" or other terms throughout the specification may be a computer or computing system or Manipulating data expressed as physical quantities, such as electronic, in a register and / or memory of a computing system of a similar computing device, to store memory, registers, or other such information in a computer system It is understood to refer to operations and / or processes that transfer, or convert to other data, which are also represented as physical quantities in the display device.

Embodiments of the invention may include an apparatus for performing the operations described herein. These devices may be specifically configured for the desired purpose, or they may be general purpose computers or digital signal processors ("DSPs") that are selectively activated or reconfigured by computer programs stored in the computer. May be included. Such a computer program may be stored in a computer readable storage medium, which is for example, a plurality of floppy disks, optical disks, CD-ROM s, magneto-optical disks, read-only memory (ROM s), a random access A computer system suitable for storing memory (RAM s ), electrically programmable read only memory (EPROM s ), electrically erasable programmable read only memory (EEPROM s ), magnetic or optical cards, or electronic instructions Including, but not limited to, any type of disc, including any other type of media that can be coupled to a bus.

  The processes and displays presented herein are not inherently related to any particular computer or other apparatus. Various general purpose systems may be used with the program according to the teachings herein, or it may prove convenient to construct a more specialized apparatus for performing the desired method. . The desired structure for these various systems will be apparent from the following description. In addition, embodiments of the present invention are not described with respect to any particular programming language. It will be appreciated that a variety of programming languages may be used to implement the teachings of the invention as described herein.

  Embodiments of the present invention will now be described, by way of example only, with reference to the following drawings.

The astigmatic axis γ of the lens in the TABO method is shown. _{Figure 7} shows the cylinder axis γ _AX in the scheme used to characterize the aspheric surface. Fig. 1 schematically shows an optical system of the eye and the lens. Fig. 1 schematically shows an optical system of the eye and the lens. Shown is ray tracing from the center of rotation of the eye. Fig. 3 shows a flow chart of an embodiment of the method according to the invention. 1 shows an example of a prior art progressive optical function. 1 shows an example of a prior art progressive optical function. 1 shows an embodiment of the method according to the invention. 1 shows an embodiment of the method according to the invention. 1 shows an embodiment of the method according to the invention. 1 shows an embodiment of the method according to the invention.

  In the sense of the present invention, the optical function corresponds to the function of the spectacle lens for providing the effect of the light rays transmitted through the spectacle lens for each gaze direction.

  Optical functions may include refractive functions, absorption of light, polarization capabilities, enhancement of contrast capabilities, and the like.

  The refractive function corresponds to the power (average power, astigmatic power, etc.) of the spectacle lens according to the gaze direction.

The term "optical design" is a term commonly used to designate a group of parameters that allow one to define the refractive function of an eyeglass lens, as known by those skilled in the ophthalmology field, and for each eyeglass lens designer It has a unique design, especially for progressive spectacle lenses. For example, the “design” of progressive spectacle lenses is not only intended to restore the ability of presbyopic people to see clearly at all distances, but also to do all physiological visual functions such as central vision, off-center vision and binocular vision It is the result of optimizing considerations and minimizing unwanted astigmatism. For example, progressive lens design
-A power profile along the main gaze direction (meridian) which the lens wearer uses during daytime activities;
-Distribution of the power distribution (average power, astigmatic power, etc.) away from both sides of the lens, ie from the main gaze direction;
including.

  These optical properties are defined and calculated by the spectacle lens designer and are part of the "design" provided by progressive lenses.

  Although the invention is not limited to progressive lenses, the terms used are shown in the drawings for progressive lenses. Those skilled in the art will be able to adapt these definitions to the case of a monofocal lens.

  A progressive lens comprises at least one and preferably two non-rotationally symmetric aspheric surfaces, including, but not limited to, progressive surfaces, regressive surfaces, toric or non-toric surfaces, for example.

で定義され、式中、Ｒ_ｍａｘはメートルで表現される局所的最大曲率半径であり、ＣＵＲＶ_ｍｉｎはディオプトリ（度数）で表現される。 As well known, the minimum curvature CURV _min is given by the following equation at any point on the aspheric surface:

_Where R _max is the local maximum radius of curvature expressed in meters, and CUR V _min is expressed in diopters (frequencies) .

で定義され、式中、Ｒ_ｍｉｎはメートルで表現される局所的最小曲率半径であり、ＣＵＲＶ_ｍａｘはディオプトリで表現される。 Similarly, the maximum curvature CURV _max is given by the following equation at any point on the aspheric surface:

_Where R _min is the local minimum radius of curvature expressed in meters, and CUR V _max is expressed in diopters.

It can be seen that when the surface is locally spherical, the local minimum curvature radius R _min and the local maximum curvature radius R _max are the same, so the minimum and maximum curvatures CURV _min and CURV _max are also the same. When the surface is aspheric, the local minimum curvature radius R _min and the local maximum curvature radius R _max are different.

From these expressions the minimum and maximum curvature _{CURV min} and _{CURV max,} minimum and maximum spherical displayed as _{SPH min} and _{SPH max} can be estimated according to the type of surface under consideration.

となり、式中、ｎはレンズの構成材料の屈折率である。 If the surface to be studied is the surface on the object side (also called the front surface), the following expression

Where n is the refractive index of the material of the lens.

となり、式中、ｎはレンズの構成材料の屈折率である。 If the surface to be examined is the surface on the eyeball side (also called the back surface), the following expression

Where n is the refractive index of the material of the lens.

で定義できる。 As well known, the mean sphere SPH _mean at any point on the aspheric surface is also given by

Can be defined by

その表面が眼球側の表面であれば、

となり、
円柱面ＣＹＬもまた、式、ＣＹＬ＝｜ＳＰＨ_ｍａｘ−ＳＰＨ_ｍｉｎ｜で定義される。 Thus, the representation of the mean sphere depends on the surface under consideration,
If the surface is the surface on the object side,

If the surface is the surface on the eyeball side,

And
Cylindrical surface CYL also _{expression, CYL} = | defined by | SPH max _{-SPH min.}

  The characteristics of any aspheric surface of the lens may also be expressed by means of locally averaged spherical and cylindrical surfaces. The surface can be considered to be locally aspheric when the cylindrical surface is at least 0.25 diopter.

With respect to the aspheric surface, the local cylinder axis γ _AX may be further defined. FIG. 1 shows the astigmatic axis γ defined in the TABO system, and FIG. 2 shows the cylinder axis γ _AX in the system defined to characterize the aspheric surface.

The cylinder axis γ _AX is the angle of orientation of the maximum curvature CURV _{max in} the selected rotational direction with respect to the reference axis. In the scheme defined above, the reference axis is horizontal (the angle of this reference axis is 0 °) and the direction of rotation is counterclockwise for each eye when looking at the wearer (0 ° ≦ 0 γ _AX ≦ 180 °). Thus, the value + 45 ° of the axis of the cylinder axis γ _AX represents an obliquely oriented axis, which extends from the upper right quadrant to the lower left quadrant when looking at the wearer.

  Furthermore, progressive multifocal lenses may also be defined by optical properties, taking into account the situation of the person wearing the lens.

  Figures 3 and 4 are schematic views of the eye and lens optics, and show the definitions used in this description. More precisely, FIG. 3 represents a perspective view of such a system, showing the parameters α and β used to define the gaze direction. FIG. 4 is a view in a vertical plane parallel to the anteroposterior axis of the head of the wearer and passing through the center of rotation of the eye when the parameter β is equal to zero.

The rotation center of the eye is indicated as Q '. An axis Q'F 'indicated by a dot-and-dash line in FIG. 4 is a horizontal axis extending to the front of the wearer through the rotational center of the eye, ie, the axis Q'F' corresponds to the main gaze field . This axis cuts the aspheric surface of the lens at a point called the fitting cross that is on the lens to allow the store clerk to position the lens in the frame. The intersection of the lens rear surface and the axis Q′F ′ is a point O. O can be a fitting loss if it is on the back side. Center 'is, and radius q' is Q vertex sphere is the posterior surface of the lens, in contact at a point with a horizontal axis. For example, the value of radius q 'of 25.5mm corresponds to a normal value, can result satisfactory obtained when wearing the lens.

A certain gaze direction, indicated by a solid line in FIG. 3, corresponds to the position of the eye in rotation about Q ′ and the point J of the vertex sphere, and the angle β is the axis Q′F ′ and the axis Q′F ′. The angle made between the projection of the straight line Q′J onto the horizontal plane including Y, and this angle is shown in the view of FIG. The angle α is the angle between the axis Q'J and the projection of the straight line Q'J on a horizontal plane containing the axis Q'F ', which is shown in the views of FIGS. Therefore, a certain gaze field corresponds to the point J of the vertex sphere or to the set (α, β). The more downward the gaze angle value is, the more downward the gaze is, and the more negative the gaze angle, the more upward the gaze.

  In a gaze direction, an image of a point M in the object space at a certain object distance is formed between two points S and T corresponding to the minimum and maximum distances JS and JT, which are sagittal and tangential local It will be the focal length. An image of a point at infinity in object space is formed at point F '. The distance D corresponds to the front and back surfaces of the lens.

Ergorama is a function that relates the normal distance of an object point to each gaze direction. Typically, in the far field, when the main gaze direction is followed, the object point is at infinity. In the near vision, when the gaze direction basically corresponding to the angle α of about 35 ° and the angle β of about 5 ° in absolute value toward the nose side is followed, the object distance is about 30 to 50 cm. For more detailed matters of possible definition of ergorama, U.S. Pat. No. 6,318,859A may be considered. This patent document describes an ergoma, its definition, and its modeling method. With respect to the methods of the present invention, a point (points) is even at infinity, may or may not. The ergorama may be a function of the wearer's refractive error or the wearer's add power.

Using these factors, it is possible to define the wearer's optical power and astigmatic power in each gaze direction. An object point M at an object distance given by the ergorama is taken into account for certain gaze directions (α, β). Object proximity ProxO, for M points on rays corresponding to that of the object space, and the reciprocal of the distance MJ between point M and the point J of the vertex sphere, is defined by the following equation.
ProxO = 1 / MJ

  This makes it possible to calculate the object proximity in the thin lens approximation for every point of the vertex sphere, which is used in the ergola determination. In the case of a real lens, the object proximity can be thought of as the reciprocal of the distance on the corresponding ray between the object point and the lens front.

For the same gaze direction (α, β), an image of a point M with certain object proximity has two points S corresponding to the minimum and maximum focal distances (which will be sagittal and tangential focal distances, respectively) It is formed between T. The value of ProxI is called the image proximity of the point M, the following equation.

Similar to the case of thin lenses, this means that for a given gaze direction and for a certain object proximity, ie for a certain point of the object space on the corresponding ray, the power Pui is of the image proximity and of the object proximity. It can be defined as the sum.
Pui = ProxO + ProxI

Using the same notation, astigmatic power Ast, for the object proximity with each gaze direction is defined as the following equation.

This definition corresponds to the astigmatism of the light beam produced by the lens. It can be understood that this definition gives classical numerical values of astigmatism in the main gaze direction. The astigmatic angle, usually called the axis, is the angle γ. Angle γ, the frame linked to the eye _{{Q ', x m, y} m, z m} are measured by. This corresponds to the angle at which the image S or T is formed, depending on the scheme used for the direction z _m in the plane {Q ′, z _m , y _m }.

Possible definitions of the refractive power and astigmatic power of the lens in the worn state can therefore be calculated as described in the article of the following document:
B. Bourdoncle et al, entitled “Ray tracing through progressive ophthalmic lenses”, 1990 International Lens Design Conference, D. T. Moore ed. , Proc. Soc. Photo. Opt. Instrum. Eng .

FIG. 5 represents a perspective view of an arrangement in which the parameters α and β are other than zero. Therefore, the effect of eye rotation can be shown by showing the fixed frame {x, y, z} and the frame {x _m , y _m , z _m } linked to the eye. The origin of frame {x, y, z} is at point Q '. Axis x is axis Q'O, which is directed from the lens towards the eye. The y-axis is vertical and directed upwards. The z-axis is such that the frames {x, y, z} are orthonormal and direct. The frame {x _m , y _m , z _m } is linked to the eye, the center of which is the point Q '. The x _m axis corresponds to the gaze direction JQ '. Hence, with respect to the main gaze direction, the two frames {x, y, z} and {x _m , y _m , z _m } are the same. It is known that the properties of certain lenses may be expressed in several ways, in particular in the surface and optically. The surface properties are therefore equivalent to the optical properties. In the case of a blank, only surface properties may be used. It should be understood that the optical properties require that the lens be machined to the wearer's prescription. In the case of spectacle lenses, on the other hand, the properties may be of the surface or optical type, both properties being able to describe the same object from two different viewpoints. Whenever the characteristics of the lens are of the optical type, this refers to the ergorama-eye-lens system described above. The term "lens" is used in the description for the sake of brevity, but this should be understood as an "ergorama-eye-lens system".

  Values in optical terms can be expressed in terms of gaze direction. The gaze direction is usually given by their downward degree and azimuth angle in the frame whose origin is the center of rotation of the eye. If the lens is mounted in front of the eye, a point called fitting cloth is placed in front of the pupil of the eye or in front of the center of rotation Q 'of the eye with respect to the main gaze direction. The main gaze direction corresponds to the situation where the wearer looks straight ahead. In the selected frame, the fitting cross therefore corresponds to a downward angle α of 0 ° and an azimuth angle β of 0 °, whether the fitting cross is located on any face of the lens, ie the rear face or the front face.

  The above description given for FIGS. 3-5 has been made with respect to central vision. In peripheral vision, when the gaze direction is fixed, the center of the pupil is considered instead of the eye rotation center, and the peripheral ray direction is considered instead of the gaze direction. When the peripheral vision is taken into consideration, the angles α and β correspond to the ray direction instead of the gaze direction.

  The wearing condition is understood as the position of the spectacle lens with respect to the wearer's eye, and is defined, for example, by wearing anteversion angle, corneal lens distance, pupil corneal distance, CRE pupil distance, CRE lens distance, and wrap angle. .

  The corneal lens-to-lens distance is the distance between the cornea and the posterior surface of the lens along the visual axis (usually horizontal) of the eye in the first eye position, for example equal to 12 mm.

  The pupillary intercorneal distance is the distance between the pupil and the cornea along the visual axis of the eye, which is usually equal to 2 mm.

  The CRE pupillary distance is the distance between the center of rotation (CRE) and the cornea, along the visual axis of the eye, for example equal to 11.5 mm.

  The CRE is the distance between the CRE of the eye and the posterior surface of the lens, for example equal to 25.5 mm, along the visual axis (usually horizontal) of the eye in the first eye position.

  The anteversion angle during wear is the eye at the first eye position with the normal to the lens rear face at the intersection of the lens back surface and the visual axis of the eye at the first eye position (usually horizontal) in the vertical plane. Angle with the visual axis, and is equal to, for example, -8 °.

  The wrap angle is defined by the normal to the lens rear surface and the visual axis of the eye at the first eye position at the intersection of the lens rear surface and the visual axis of the eye at the first eye position (usually horizontal) in a horizontal plane. And an angle between, for example, equal to 0 °.

  An example of a standard wearer situation is: -8 ° wearing anteversion, 12 mm corneal lens distance, 2 mm pupil inter-corner distance, 11.5 mm CRE inter-pupil distance, 25.5 mm CRE lens It may be defined by the distance and the wrap angle of 0 °.

  Other conditions may be used. Wearing conditions may be calculated from a ray tracing program for a lens.

As shown in FIG. 6, the method according to the invention at least
-Wearer data providing step S1;
An optical function determination step S2;
including.

In the consumer data providing step S1, consumer data is provided.

The wearer data includes at least an indicator of the ophthalmic prescription of the wearer.

Typically, the ophthalmic formulation of the wearer is provided. Alternatively, information may be provided that may determine such an ophthalmic prescription, which may be provided with an indicator, for example, to allow the wearer's ophthalmic prescription to be determined from a database and / or a lookup table.

The wearer's ophthalmologic prescription is the refractive power determined by the ophthalmologist to correct the visual impairment of the individual, for example by means of a lens placed in front of the eye, the degree of astigmatism and, if relevant, the addition power. It is an optical characteristic group. In general, the prescription of the progressive addition lens comprises numerical values of the spherical power and of the astigmatic power at the far field point and, where appropriate, the value of the addition power.

According to an embodiment of the present invention, said wearer's prescription comprises cylindrical prescription values and / or cylindrical prescription axis values and / or spherical prescription values.

Furthermore, the wearer data includes an indication of hearing sensitivity of the wearer. Typically, the auditory sensitivity of the wearer is provided. Alternatively, such auditory sensitivity of the determination may be possible information that may provide, for example, an indicator that allows determination of the hearing sensitivity of the wearer from the database and / or look-up table may be provided .

The wearer data, visual display of a voice message, may contain particularly further indication of the impact of a person to face and the wearer has on the understanding by the wearer of Could conversation.

Typically, the hearing sensitivity of the wearer and / or visual indication effect of relative understanding of the voice message by the wearer may be determined by objective and / or subjective test.

Objective tests are normally based on the quantification by specialized equipment, on the other hand, the subjective test is based on the measurement and / or subjective judgment of the individual facing the provided by that phenomenon.

Typically, audiometry, i.e. a series of measurements is determined hearing profile of human, it may be carried as an indicator of visual display effects on the understanding of the voice message auditory sensitivity and / or wearer of the wearer . In other words, audiometry, may be performed in order that provides the status of correct hearing of the wearer.

  Among the most common hearing tests, tone tests and / or speech frequency tests may be performed.

  Typically, the tone test is performed by measuring through the air or bone conduction hearing threshold for all speech frequencies between 125 and 6000 Hz for air conduction and 250 to 4000 Hz for bone conduction.

  The air conduction may use headphones or speakers, for example, a meter may be installed in front of the wearer.

  For bone conduction, for example, a vibrator using a tuning fork may be used.

  According to an embodiment of the present invention, the auditory sensitivity of the wearer may be determined by a test that assesses speech comprehension in a noisy environment.

There are various tests for evaluating the ability of a person who can hear speech in a noisy environment, for example an acceptable noise level test. An example of such a test is described in the following document.
“Comparison of Speech Perception in Noise Background with Acceptance of Background Noise in Aided and unaided conditions.” Anna K. Nabelek, Joanna W. Tampas, and Samuel B. Burchfield. Journal of Speech, Language, and Hearing Research, October 2004, Vol. 47, 1001-1011 .

  According to an embodiment of the present invention, the auditory sensitivity of the wearer may be determined by means of a lifestyle questionnaire related to hearing in everyday listening situations.

Application uHear (registered trademark) provides an example of such a life questionnaire, which includes the question of the 12 items, provides a score based on the answers. For example, the validity of this questionnaire has been scientifically confirmed in the following document.
“The Hearing-Dependent Daily Activities Scale to Evaluate Impact of Hearing Loss in Older People”. Lopez-Torres Hidalgo J, et al. Ann Fam Med. 2008 Sep; 6 (5): 441-447 .

According to an embodiment of the present invention, the auditory sensitivity of the wearer may be determined by a test of a facial expression reading test .

The term “labo-facial reading” is understood by the visual interpretation of a person's conversation by the movements of his face, in particular his lips and tongue. For example, a reading test of facial expressions includes lip reading, also called reading, which corresponds to understanding a person's conversation by visually interpreting the movement of said person's lips .

  Typically, it is possible to quantify the degree of comprehension thanks to software that provides lip-teaching training using video footage of life, with and without visual display. With such software it is possible to assess the loss or gain based on visual performance and / or the auditory and speech environment (SNR).

GERIP (R) lip reading software (Ref.VS01) may be used to test the reading test for expression of such face.

Depending on the wearer's hearing sensitivity indicator, different results may be obtained. For example, the auditory sensitivity of the wearer may reveal abnormal loss of sensation (meaning that the auditory sensitivity of the wearer is lower than the standard auditory sensitivity), for example the auditory sense associated with the wearer's aging The possible loss of auditory sensitivity associated with the gain of clarity when the normal loss of sensitivity may become apparent or the wearer has better visualization of the labo-facial indication (wear It may become apparent whether the person has an abnormal loss of hearing sensitivity or whether it has a normal loss).

In all these cases it is possible to propose to the wearer the specific optical solution proposed in step S2 of FIG. 6 rather than the standard optical solution, which solution Are particularly recommended when they have unusual auditory sensitivities, or when tests of the facial expression reading test show significant gains.

In the optical function determining step S2, the optical function compatible spectacle lenses to the wearer is determined based on the index of the ophthalmic formulation of at least wearer's data, i.e. an indicator of hearing sensitivity wearer wearer.

Typically, based on the wearer data, lens designers, so to provide ophthalmic correction, to improve the understanding of the wearer of the hearing, voice message conversation due persons are facing the particular wearer An adapted optical function can be provided.

According to an embodiment of the present invention, during the optical function determination step, the optical function comprises an area adapted to facilitate a reading examination of the facial expression of the wearer.

  For example, the lens designer may provide a progressive spectacle lens with an extended intermediate distance viewing area. The intermediate distance vision area corresponds to the area or area of the spectacle lens adapted to the intermediate distance vision, for example between 70 cm and 200 cm.

  Therefore, by enlarging the intermediate distance vision area, the wearer can therefore obtain a better vision for reading the lips, ie the astigmatism of that area is smaller, and by means of the large area its own. The dependence on gaze position / direction when looking at the interlocutor is reduced.

  This solution may be based on the optimization of the progressive ophthalmic design in the intermediate distance vision area, which improves the performance capacity or the contrast sensitivity or the recognition of curvature and / or movement.

  This optimization is done taking into account the ametropia and wearing conditions.

  The optical function determination step may include a selection step in which an optical function is selected from a predetermined optical function group based on the wearer data.

  For example, based on the wearer's ophthalmic prescription, a set of adapted optical surface combinations provides a predetermined optical function selected from a predetermined optical function group by any known selection method. Based on the wearer's hearing sensitivity, a suitable modified surface is selected. The selected modification surface will be added to at least one surface of the set of optical surfaces to be adapted to modify the optical function of the spectacle lens in order to expand the intermediate distance viewing area.

  Figures 7a and 7b show the optical characteristics of a prior art progressive power lens with a far field power of 1.0 D and an addition power of 2 D under standard wearing conditions.

  FIG. 7a shows the average power between the minimum and maximum power curves along the meridian. The diopter changes in the x-axis, and the y-axis shows the height on the lens corresponding to the angle alpha in degrees.

  FIG. 7 b shows astigmatic power contours, ie the lines formed by the points whose astigmatic powers have the same numerical value. The x-axis and y-axis show spatial coordinates in degrees.

Figures 8a and 8b show a far-field power of 1 with an intermediate distance field of view adapted to facilitate the reading of the reading test of the wearer's facial expression in the same standard wearing conditions as in Figures 7a and 7b. 0D shows the optical characteristics of a 2D progressive addition lens.

  FIG. 8a shows the mean power curve between the minimum and maximum power curves along the meridian. The diopter changes in the x-axis and the y-axis shows the height above the lens in degrees.

  FIG. 8 b shows astigmatic power contours, ie the lines formed by the points whose astigmatic powers have the same numerical value. The x-axis and y-axis show spatial coordinates in degrees.

  As shown in FIGS. 8a, 8b, the modified power function has an intermediate distance viewing area magnified around an alpha = 18 °. Typically, the distance 0.5 between the astigmatic power contours is a distance of 12 °, whereas in prior art designs the distance of such contours is a distance of 6 ° around alpha = 18 ° is there.

According to another embodiment of the present invention, in order to increase the visual comfort of the wearer, in particular advanced presbyopic patients, with respect to the slightly downward gaze direction corresponding to the labo-facial direction , In order to provide a higher addition power than the progressive optical function of the optical function, it is possible to determine the optical function which starts earlier in the progression or which has a steeper slope.

  Advantageously, the wearer can reach an intermediate distance viewing area matching the lab-facial orientation with less head travel in the longitudinal direction.

  Figures 9a and 9b show the optical characteristics of such a progressive power lens with a far field sphere of 1.0 D and an addition of 2 D, under the same standard wearing conditions as in Figures 7a and 7b.

  FIG. 9a shows the mean power curve between the minimum and maximum power curves along the meridian. The diopter changes in the x-axis and the y-axis shows the height above the lens in degrees.

  FIG. 9 b shows astigmatic power contours, ie lines formed by points whose astigmatic powers have the same numerical value. The x-axis and y-axis show spatial coordinates in degrees.

  Compared to the optical function shown in FIG. 7a, it can be seen that the progression has a steeper slope, which allows the wearer's eye to more easily reach the intermediate distance region matching the lab-facial direction.

  According to one embodiment of the present invention for reducing astigmatism in the lab-facial direction, the onset of progression is lower, eg, 1 mm to 4 mm lower, than in the case of a conventional progressive spectacle lens, eg, a conventional progression It can provide an optical function 2 mm lower than in the case of a spectacle lens. In other words, the far vision area will be consumed as it covers the lab-facial direction. This will be especially dedicated to young presbyopic patients who have higher vision control ability than 1 D and can follow lip movements during speech without adjusting their head position in the intermediate distance vision area .

According to an embodiment of the present invention, a single focus optical function adapted for an intermediate distance field of view may be provided. Advantageously, the spectacle lens with such an optical function provides a wide field of view at 1 m and is particularly suitable for lab -facial vision .

  According to an embodiment of the present invention, an eyeglass lens having lower addition power (≦ 1 dp) optical function may be provided. Such an embodiment allows a person other than presbyopia with a loss of hearing sensitivity to be more perceptible at a communication distance of, for example, a distance of 60 cm to 1 m while easing its visual acuity adjustment function.

  According to an embodiment of the present invention, the optical function may be provided by an active power lens, for example using an activatable power area in a spectacle lens adapted for an intermediate field of view, this power being Provide enrollment power when needed to make facial metrics more visible (eg, in consultation with others), otherwise disabled.

  Furthermore, such a solution is also interesting for the normal hearing wearer, even for the purpose of protection, in order to increase its aural visual comfort.

  According to an embodiment of the present invention, the optical function determination step may include the step of determining a transmission function based on the wearer data.

  Typically, spectacle lenses can be tinted to enhance lip contrast when viewed through the spectacle lens.

  For example, red may be enhanced. Thus, for example, by providing an orange filter, the wavelength corresponding to red lambda greater than 650 nm is not absorbed and the other wavelengths between 380 nm and 650 nm are absorbed.

  Alternatively, the red color of the lips may be absorbed by providing a red absorption filter between 650 and 780 nm, such as a green color filter.

  These filters may be tinted slightly, for example according to the ISO 8980-3 standard, for example category 0-1, in order to protect the aesthetics of the lens. The coloring may further be localized in the lens, for example in the upper part, or the spectacle lens may be beveled.

Colored solar, polarized, photochromic, electrochromic lenses may be further provided to optimize the intermediate distance viewing area which is advantageous for facial expression reading inspection . For example, by providing a bi-gradient, far-field and near-field area dark intermediate distance vision area.

  The invention further relates to a pair of spectacle lenses adapted to the wearer, at least one of the lenses having an optical function determined by the method according to the invention.

  Such a robust lens may be manufactured using standard manufacturing methods and equipment, or an active spectacle lens whose optical function can be adapted to enable the wearer of the spectacle lens to better understand the voice message It may be

  Typically, the invention may relate to a programmable lens device comprising a programmable lens, an optical function controller, a memory and a processor. The programmable lens has an optical function and extends between at least one eye of the wearer and the real-world scene when the wearer uses the device. The optical function controller is configured to control the optical function of the programmable lens. The memory contains program instructions that are executed by the processor to perform the steps of the method of the present invention.

  The present invention has been described using the embodiments without limiting the overall inventive concept.

In particular, it will be appreciated by those skilled in the art that many other modifications may be made by reference to the above described exemplary embodiments which are mentioned by way of example only and which do not limit the scope of the invention which is determined solely by the appended claims Changes will be recalled.

  In the claims, the word "comprising" does not exclude other elements or steps, and the indefinite article (a, an) does not exclude a plurality. The mere fact that different features are recited in mutually different dependent claims does not indicate that a combination of these features can not be used advantageously. Any reference signs in the claims should not be construed as limiting the scope of the present invention.

Claims (17)

In the computer-implemented method for determining the optical function of a spectacle lens adapted to the wearer,
A wearer data providing step of providing wearer data including at least an indicator of the auditory sensitivity of the wearer and an indicator of the ophthalmic prescription of the wearer;
An optical function determining step in which an optical function adapted to the wearer is determined based on at least the wearer data;
Method including.   The method according to claim 1, wherein the wearer data further includes an indicator of an influence of a visual indicator on an understanding of the voice message by the wearer. The method according to claim 1, wherein the optical function determination step is performed such that the optical function includes an area adapted to facilitate a reading examination of the facial expression of the wearer. The hearing sensitivity of the wearer provided during wearer data providing step is determined by at least one objective testing method according to any one of claims 1 to 3. The objective test is a sensory test of the audio frequency range, the method of claim 4. Wherein the hearing sensitivity of the wearer data the provided Ru provided during step wearer is determined by at least one subjective test method according to any one of claims 1 to 5. The subjective tests described below,
-Evaluation of speech comprehension in noisy environments-Life questionnaire on hearing in everyday listening situations-Test according to claim 6 selected from one of the tests consisting of a test of reading tests of facial expressions Method.   The method according to any one of claims 1 to 7, wherein the optical function determination step includes the step of selecting an optical function from a predetermined optical function group based on the wearer data.   The method according to any one of the preceding claims, wherein said optical function determination step comprises the step of determining a transmission function based on said wearer data.   The method according to any one of the preceding claims, wherein said optical function determining step comprises determining a refractive function based on said wearer data. Wearer voice message of the spectacle lens, the use of the wearer and are for a better understanding of the voice message person emitted that faces, spectacle lenses including the region adapted to at least the intermediate distance vision. Wearer voice message spectacle lenses, the wearer and to allow better understanding of the voice message emitted by the person who is facing, spectacle lenses including the region adapted to at least the intermediate distance vision. At least the intermediate distance vision region adapted for intermediate distance vision, the spectacle lens adapted to the wearer, the transmission function of the spectacle lens, for the intermediate distance of the person visible through the viewing area lips to appear better A spectacle lens arranged to improve the reading examination of the facial expression of the wearer.   The spectacle lens according to claim 13, wherein the spectacle lens is colored to enhance the contrast of the lips of a person viewed through the spectacle lens.   A computer program product comprising one or more stored sequences of instructions accessible by a processor, which when executed by the processor causes the processor to carry out the steps of the method according to any one of the claims 1-10 .   A computer readable medium executing one or more sequences of instructions of the computer program product according to claim 15. In a pair of spectacle lenses adapted to the wearer:
A pair of spectacle lenses, wherein at least one of the spectacle lenses has an optical function determined by the method according to any one of claims 1 to 10.